Method and apparatus to ensure consistent left ventricular pacing

ABSTRACT

A method of operating a cardiac therapy system to deliver cardiac resynchronization therapy (CRT) pacing that includes pacing both ventricles or pacing only the left ventricle is described. Delivery of the CRT pacing to one or both ventricles is scheduled for a cardiac cycle. If an intrinsic depolarization of a ventricle is detected during a pacing delay of the ventricle, then the scheduled CRT pacing to the ventricle is inhibited for the cycle. The intrinsic interval of the ventricle, such as the intrinsic atrioventricular interval concluded by the intrinsic depolarization, is measured. During a subsequent cardiac cycle, the pacing delay of the ventricle is decreased to be less than or equal to the measured intrinsic interval. Capture of the ventricle is verified after pacing is delivered during the subsequent cardiac cycle.

RELATED APPLICATION

This application a divisional of U.S. patent application Ser. No.12/435,915, filed on May 5, 2009, to which priority is claimed pursuantto 35 U.S.C. §120, and claims the benefit of Provisional PatentApplication Ser. No. 61/126,859 filed on May 7, 2008, to which priorityis claimed pursuant to 35 U.S.C. §119(e), and which are both herebyincorporated herein by reference in their entirety.

FIELD OF THE INVENTION

The present invention relates generally to cardiac pacing therapy, andmore specifically, to methods and systems for determination of pacingparameters to ensure consistent capture for left ventricular pacingduring cardiac resynchronization therapy.

BACKGROUND OF THE INVENTION

Congestive heart failure is the loss of pumping power of the heart,resulting in the inability to deliver enough blood to meet the demandsof peripheral tissues. Congestive heart failure (CHF) may causeweakness, loss of breath, and build up of fluids in the lungs and otherbody tissues.

CHF is usually a chronic, long term condition, but can occur suddenly.It may affect the left heart, right heart or both sides of the heart.Heart failure has a variety of causes, primarily ischemic heart disease.The deterioration of the muscles of the heart caused by ischemic heartdisease result in an enlargement of the heart and reduced contractility.The reduced contractility decreases the cardiac output of blood andtypically results in an increased heart rate. Cardiac conduction pathblock may also occur in the enlarged heart tissue, causing the signalsthat control the heart rhythm to travel more slowly through the enlargedheart tissue. For example, if CHF affects the left ventricle, signalsthat control the left ventricular contraction are delayed, and the leftand right ventricles do not contract simultaneously. Non-simultaneouscontractions of the left and right ventricles decrease the pumpingefficiency of the heart.

CHF may be treated by medication and/or by cardiac pacing therapy.Pacing therapy to promote synchronization of heart chamber contractionsfor improved cardiac function is generally referred to as cardiacresynchronization therapy (CRT). Some cardiac pacemakers are capable ofdelivering CRT by pacing multiple heart chambers. Pacing pulses aredelivered to the heart chambers in a sequence that causes the heartchambers to contract with enhanced synchrony, increasing the pumpingpower of the heart and delivering more blood to the peripheral tissuesof the body. In the case of dysynchrony of right and left ventricularcontractions, a CRT pacing may be used to resynchronize the left andright ventricles. Successful pacing of the left ventricle is critical toachieve the benefit of CRT. Bi-atrial pacing or pacing of all four heartchambers may also be used.

Pacing therapy is delivered by pacing one or more heart chambers usingpacing delays that control the timing and sequence of the pacing pulses.Appropriate specification of these pacing delays is desirable to achieveimprovement of cardiac function through enhanced synchrony. For thereasons stated above, and for other reasons stated below which willbecome apparent to those skilled in the art upon reading the presentspecification, there is a need in the art for methods and systems thatprovide for determination of delays used for CRT pacing. The presentinvention fulfills these and other needs.

SUMMARY OF THE INVENTION

The present invention is directed to systems and methods for determiningcardiac pacing parameters for cardiac resynchronization therapy (CRT)pacing includes at least pacing a left ventricle.

One embodiment of the invention involves a method of operating a cardiactherapy system to deliver cardiac resynchronization therapy (CRT) pacingthat includes pacing both ventricles or pacing only the left ventricle.Delivery of the CRT pacing to one or both ventricles is scheduled for acardiac cycle. If an intrinsic depolarization of a ventricle is detectedduring a pacing delay of the ventricle, then the scheduled CRT pacing tothe ventricle is inhibited for the cycle. The intrinsic interval of theventricle, e.g., the intrinsic atrioventricular interval concluded bythe intrinsic depolarization, is measured. During a subsequent cardiaccycle, the pacing delay of the ventricle is decreased to be less than orequal to the measured intrinsic interval. Capture of the ventricle isverified after pacing is delivered during the subsequent cardiac cycle.

According to various aspects of the invention, the pacing delay mayinvolve one or more of a right atrioventricular delay, a leftatrioventricular delay, and an interventricular delay.

The pacing delay may remain at the decreased value for a number ofsubsequent cardiac cycles or may be further decreased if capture is notverified for subsequent cycles. If capture is confirmed, the pacingdelay may be gradually increased, e.g., incrementally increased by apredetermined amount, during one or more subsequent cardiac cycles.

According to one implementation, the CRT pacing is scheduled to bedelivered to both left and right ventricles. The CRT pacing to the leftor right ventricles may be inhibited by an intrinsic depolarization thatoccurs during the pacing delay of that ventricle. For example, ascheduled right ventricular pace may be inhibited by an intrinsic rightventricular depolarization that occurs during a right ventricular pacingdelay. A scheduled left ventricular pace may be inhibited by anintrinsic left ventricular depolarization that occurs during a leftventricular pacing delay. Paces to both the left and right ventriclesmay be inhibited if intrinsic depolarizations of both ventricles occurduring their respective pacing delays. If pacing is inhibited to aventricle, the intrinsic interval of that ventricle is measured. Asubsequent pacing delay for the ventricle is decreased based on theintrinsic interval measured for that ventricle.

According to a further aspect, if no intrinsic depolarization of theventricle is detected during the pacing delay, then the CRT pacing isdelivered as scheduled. A cardiac response to the pacing (e.g., capture,fusion, or non-capture of the ventricle with or without intrinsicactivation) is determined. The pacing delay of the ventricle is adjustedfor the subsequent cardiac cycle based on the cardiac pacing response.For example, the same pacing delay may be maintained on subsequentcardiac cycles so long as capture is detected. In anotherimplementation, the pacing delay may be increased during subsequentcycles if capture is detected and the pacing delay was previouslydecreased responsive to detection of an intrinsic depolarization. Iffusion is detected, the pacing delay may be incrementally decreased. Ifnon-capture is detected, one or more pacing parameters affecting pacingenergy output (e.g., current, voltage, pulse duration, and/or pulsewaveform) may be adjusted.

According to a further aspect, cardiac rate may be measured, forexample, by measuring the intrinsic atrial rate. The pacing delay may beadjusted based on both the cardiac pacing response and measured cardiacrate. In one implementation, adjusting the pacing delay comprisesadjusting the pacing delay using a look-up table of pacing delaysindexed by cardiac rate. The pacing delay values obtained from the lookup table may be additionally increased or decreased beat by beat basisaccording to whether an intrinsic depolarization occurred during theprevious cardiac cycle and/or on the capture status of a previous cycle.

Another embodiment of the invention involves a method of setting pacingdelays for cardiac resynchronization therapy (CRT) pacing that includespresentation of information to a human analyst regarding relationshipsbetween the pacing delays, measured cardiac rate, measured intrinsicinterval and the cardiac pacing response for a plurality of cardiacintervals. These parameters are determined for a plurality of cardiacintervals and are stored. The stored information is analyzed todetermine at least one recommended pacing delay. The at least onerecommended pacing delay is presented to a human analyst via a userinterface.

According to one implementation, the stored information may be analyzedto develop a look up table of recommended pacing delays based on theprevious pacing delays, measured cardiac rate, the measured intrinsicinterval; and/or the cardiac pacing response for the plurality ofcardiac intervals.

Yet another embodiment of the invention is directed to a cardiac therapysystem capable of delivering cardiac resynchronization therapy (CRT)pacing that involves pacing at least the left ventricle. The systemincludes electrodes configured to electrically couple to right and leftventricles. Sensing circuitry is coupled to the electrodes and isconfigured to sense intrinsic depolarization signals and other cardiacsignals via the electrodes. Pacing circuitry is configured to generatepacing pulses deliverable through the electrodes. The system includescardiac response classification circuitry that is capable of determininga cardiac response to the pacing pulses. The system also includes pacingcontrol circuitry that schedules pacing to be delivered relative apacing delay to at least one ventricle during a cardiac cycle. If anintrinsic depolarization is detected during the pacing delay, thescheduled CRT pacing to the ventricle is inhibited. If an intrinsicdepolarization occurs during the pacing delay, the intrinsic interval(e.g., atrioventricular interval or interventricular interval that isinitiated or concluded by the intrinsic depolarization) is measured. Thepacing delay of a subsequent cardiac cycle is decreased to be less thanor equal to the measured intrinsic interval.

For example, if the pacing control circuitry schedules delivery of CRTpacing to both left and right ventricles, one or both of the paces maybe inhibited by intrinsic depolarizations occurring within therespective pacing delays of the left and right ventricles. If eitherpace is inhibited, the intrinsic interval for that ventricle is measuredand is used to decrease subsequent pacing delays for that ventricle. Ifboth paces are inhibited, the intrinsic intervals for both ventriclesmay be measured and used to decrease subsequent pacing delays for theventricles.

The pacing control circuitry may further decrease the pacing delay for aventricle during subsequent cardiac cycles until the cardiac responseclassification circuitry determines that capture occurs. When capture isdetected, the pacing control circuitry may increase the pacing delay foreach subsequent cycle until the initial pacing delay is achieved.

If an intrinsic depolarization of the ventricle is not detected duringthe pacing delay of the cardiac cycle, the CRT pacing is delivered asscheduled. During subsequent cardiac cycles, a pacing delay for aventricle may be based on the cardiac pacing response of that ventricleto the delivered CRT pacing. For example, the cardiac responseclassification processor may discriminate between capture, fusion, andnon-capture of the ventricle. The pacing delay of the ventricle for thesubsequent cardiac cycle is adjusted based on the cardiac pacingresponse. In one implementation, if capture is detected as the pacingresponse, the pacing delay may be maintained at the same value forsubsequent cycles. If fusion is determined to be the pacing response,the pacing delay may be incrementally decreased for subsequent cycles toavoid fusion responses.

The cardiac therapy system may also include a memory in whichinformation such as measured cardiac rate, measured intrinsic intervals,and cardiac pacing response for a plurality of cardiac cycles is stored.The pacing control circuitry, which may be fully implantable, or mayhave internal and external components operating in cooperation, mayanalyze the stored information to determine one or more pacing delaysfor the CRT pacing. The analysis may take into account one or more ofprevious pacing delays, the measured cardiac rate, the measuredintrinsic intervals, and the cardiac pacing responses of one or bothventricles for the plurality of cardiac cycles.

In one implementation, the cardiac therapy system includes a memoryconfigured to store information related to the measured cardiac rate,the measured intrinsic interval, and the cardiac pacing response for aplurality of cardiac intervals. The memory may store a look up tableused to adjust pacing delays beat by beat. The system may also includean external user interface configured to present to a human analystinformation indicating relationships between the previous pacing delays,measured cardiac rates, the measured intrinsic intervals and/or thecardiac pacing responses for the plurality of cardiac intervals. Thepacing control circuitry may analyze the information stored in thememory to determine at least one recommended pacing delay for asubsequent cardiac cycle. One or more recommended pacing delays canpresented to a human analyst via a user interface to allow the humananalyst to accept or override the recommended pacing delays. Therecommended pacing delays may be one or more of right atrioventriculardelay, a left atrioventricular delay, and an interventricular delay.

The cardiac therapy system may also include a sensor configured togenerate an output based a patient's hemodynamic need. The pacingcontrol circuitry may adjust the pacing delay based on the sensoroutput, thus taking into account the patient's hemodynamic need whenadjusting the pacing delay.

The above summary of the present invention is not intended to describeeach embodiment or every implementation of the present invention.Advantages and attainments, together with a more complete understandingof the invention, will become apparent and appreciated by referring tothe following detailed description and claims taken in conjunction withthe accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A and 1B are timing diagrams illustrating pacing delays foratrial tracking or atrioventricular sequential CRT pacing;

FIG. 2 is a flow diagram illustrating a process for adjusting CRT pacingdelays based on LV capture status in accordance with embodiments of theinvention;

FIG. 3A is a flow diagram illustrating a process for adjusting CRTpacing delays based on capture status in conjunction with atrial rate inaccordance with embodiments of the invention;

FIG. 3B illustrates a process of decreasing a pacing delay following asensed beat and then gradually lengthening the pacing delay duringsubsequent beats to promote consistent LV pacing in accordance withembodiments of the invention;

FIGS. 4A-4C, and 5 illustrate bar graphs summarizing stored informationrelated to various cardiac responses during pacing which may bedisplayed to facilitate determination of CRT pacing delays in accordancewith embodiments of the invention;

FIG. 6 illustrates a user interface component that may be operated by auser to confirm suggested pacing delays or to adjust pacing delays inaccordance with embodiments of the invention;

FIG. 7 is a view of an implantable cardiac device that may be used forCRT pacing using pacing delays determined in accordance with embodimentsof the invention; and

FIG. 8 is a block diagram of a cardiac system capable of utilizingcardiac pacing response status and rate information to adjust pacingdelays for consistent LV pacing in accordance with embodiments of theinvention.

While the invention is amenable to various modifications and alternativeforms, specifics thereof have been shown by way of example in thedrawings and will be described in detail below. It is to be understood,however, that the intention is not to limit the invention to theparticular embodiments described. On the contrary, the invention isintended to cover all modifications, equivalents, and alternativesfalling within the scope of the invention as defined by the appendedclaims.

DETAILED DESCRIPTION OF VARIOUS EMBODIMENTS

In the following description of the illustrated embodiments, referencesare made to the accompanying drawings, which form a part hereof, and inwhich is shown by way of illustration, various embodiments in which theinvention may be practiced. It is to be understood that otherembodiments may be utilized, and structural and functional changes maybe made without departing from the scope of the present invention.

Systems, devices or methods according to the present invention mayinclude one or more of the features, structures, methods, orcombinations thereof described hereinbelow. For example, a device orsystem may be implemented to include one or more of the advantageousfeatures and/or processes described below. It is intended that suchdevice or system need not include all of the features described herein,but may be implemented to include selected features that provide foruseful structures and/or functionality. Such a device or system may beimplemented to provide a variety of therapeutic or diagnostic functions.

Embodiments of the invention are directed to systems and methods forensuring or promoting consistent ventricular pacing through adjustmentof ventricular pacing delays and/or pacing energy parameters. Adjustmentof the pacing delays may involve adjusting one or more atrioventriculardelays and/or interventricular delay, for example. Adjustment of thepacing energy parameters may involve adjusting one of more of thevoltage, current, duration, and/or waveform of the pacing pulses. Thetechniques described herein are particularly useful for setting pacingdelays and/or pacing energy to enhance delivery of cardiacresynchronization pacing therapy (CRT).

CRT involves pacing stimulation applied to one or more heart chambers ina manner that compensates for conduction delays and improves pumpingaction. CRT may involve pacing one or both atria and/or one or bothventricles. For example, when CRT pacing is applied to one or bothventricles, a more coordinated contraction of the ventricles is achievedwith improved pumping efficiency and increased cardiac output. CRT canbe implemented in certain patients by pacing in both left and rightventricles, or in the left ventricle (LV) or the right ventricle (RV)alone. For example, in some CRT configurations, an RV pace may bedelivered following an appropriate pacing delay relative an atrial senseor pace and an LV pace may be delivered after an appropriate delayinitiated relative to a right ventricular (RV) or pace or sense or maybe delivered after an appropriate delay initiated relative to the atrialsense or pace. In some configurations, resynchronization pacing mayinvolve biventricular pacing with the paces to right and left ventriclesdelivered either simultaneously or sequentially, with aninterventricular delay (IVD) between the paces. The IVD is sometimesreferred to as a biventricular offset or LV offset

In one example of CRT, atrial paces and senses trigger anatrioventricular delay (AVD_(R)) which upon expiration results in a paceto the right ventricle. A pace to the left ventricular is delivered atthe specified IVD with respect to expiration of the AVD_(R). This pacingscenario may alternatively be described in terms of atrioventriculardelays between the atrial sense or pace and the scheduled pace to theright ventricle (AVD_(R)) and a separate atrioventricular delay(AVD_(L)) which occurs between an atrial sense or pace and the scheduledpace to the left ventricle.

CRT pacing is often implemented in an inhibited demand mode wherein apacing pulse is delivered to a cardiac chamber if no intrinsic beat isdetected in the cardiac chamber prior to expiration of a pacinginterval. In ventricular CRT pacing, ventricular pacing is typicallyapplied to both ventricles, although in some implementations only oneventricle, such as the LV, may be paced. In some implementations, CRTpacing involving biventricular pacing or LV only pacing may beimplemented in atrial tracking or AV sequential pacing modes. In thesepacing modes, a sense or pace initiates an atrioventricular delay and,if no intrinsic ventricular depolarization is sensed prior to expirationof the atrioventricular delay, ventricular pacing is delivered.

An AVD_(R) and AVD_(L) having the same duration during a cardiac cycleresults in simultaneous pacing of the right and left ventricles. If theduration of the AVD_(R) is different from the duration of the AVD_(L),the result is pacing with an interventricular delay (IVD) which is thedifference between the AVD_(L) and the AVD_(R). An AVD_(R) and apositive IVD (AVD_(L)>AVD_(R)) is illustrated in FIG. 1A. As can beappreciated from consideration of FIG. 1A, this pacing implementationproduces pacing delivered first to the right ventricle and then to theleft ventricle. An AVD_(R) with a negative IVD (AVD_(L)<AVD_(R)) isillustrated in FIG. 1B. In this pacing implementation a pace isdelivered to the left ventricle first followed by a pace to the rightventricle. In inhibited demand pacing, if an intrinsic right ventriculardepolarization occurs during the AVD_(R), then at least the scheduledright ventricular pacing is inhibited and possibly both RV and LV pacesare inhibited. Correspondingly, if an intrinsic left ventriculardepolarization occurs during the AVD_(L), then at least the scheduledleft ventricular pacing is inhibited.

One skilled in the art will recognize that CRT pacing described in termsof timing intervals AVD_(R), AVD_(L) may alternatively be described interms of timing intervals AVD_(R) and IVD, where IVD=AVD_(L)−AVD_(R).For the purposes of the discussion herein, CRT pacing delays aredescribed in terms of AVD_(R) and AVD_(L). This choice of terminology ismade for purposes of explanation and does not impose any limitation uponthe methods or devices described herein. Those skilled in the art willreadily understand that the invention may alternatively be described andimplemented using the terminology of AVD_(L) and IVD or AVD_(R) and IVD.

Methods, devices, and systems of the present invention provide fordetermination of the pacing delays implemented in CRT pacing therapy,such as the AVD_(R) and/or AVD_(L) used for cardiac resynchronizationtherapy. According to embodiments of the invention, adjustments made toone or more of the right and left ventricular pacing delays and rightand left ventricular pacing energies are based on intrinsic conductiondata and cardiac pacing response determination and also take intoaccount heart rate. Embodiments of the invention are described in termsof CRT pacing involving biventricular pacing or LV only pacing, althoughthe concepts apply as well to biatrial or four chamber pacing.

The flow diagram of FIG. 2 illustrates a process for setting CRT pacingparameters in accordance with embodiments of the invention. In thisexample, cardiac resynchronization therapy (CRT) pacing that involves atleast LV pacing is implemented along with beat by beat LV pacingresponse determination. An algorithm that determines the cardiac pacingresponse beat by beat is used to determine the responses of the LV or RVto the delivered paces. Pacing parameters including pacing delays and/orpacing energy are adjusted beat by beat based on the cardiac response toRV and LV pacing, or LV only pacing (e.g., capture, fusion, non-capture,etc.) and intrinsic interval measurements that indicate cardiac tissueconduction delays.

According to this process, CRT pacing including LV pacing is scheduled205 for each cardiac cycle. As discussed in more detail above, CRTpacing includes scheduling the delivery of at least an LV pace relativeto a pacing delay, denoted herein as the AVD_(L). If an LV intrinsicevent is sensed 210 during the AVD_(L) and prior to delivery of the LVpace, pacing to the LV is inhibited 215 and the conduction intervalbetween the atrial event and the intrinsic LV depolarization (AVI_(L))is measured 220. The AVD_(L) is decreased 225 based on the measuredconduction interval. For example, the AVD_(L) may be decreased by anamount being slightly greater than the difference between the currentAVI_(L) and the AVD_(L). After decreasing the AVD_(L) on the next cycle,LV capture is confirmed following delivery of the pacing pulse. If theLV pace is again inhibited on subsequent beats, the pacing delay may bedecreased again until LV capture is detected.

If no intrinsic LV depolarization occurs 210 prior to expiration of thepacing delay, then LV pacing is delivered 230 as scheduled. Delivery ofthe LV pace may be followed by one of the four situations illustrated inFIG. 2. The LV may be captured by the pace, a fusion beat may result, orthe LV pace may not produce capture. Non-capture of the LV may occurwith or without an intrinsic depolarization during the cardiac cycle.

In some implementations, the cardiac pacing response of a ventricle maybe determined by analyzing the morphology of the cardiac signal sensedfollowing delivery of the pacing pulse. The sensed cardiac signal may becompared to templates or other types of references that characterize anexpected morphology for various types of pacing responses.Morphology-based capture detection may be used to analyze peakamplitudes and/or peak timing of the cardiac signals within a capturedetection window to determine if the features of he sensed cardiacsignals are consistent with those expected for capture, fusion, ornon-capture with intrinsic activation, for example. Non-capture withoutintrinsic activation may be determined if the cardiac signals do notsurpass a threshold amplitude. Morphological analysis for cardiacresponse classification may be applied separately to the left and rightventricles based on the left and right cardiac signals sensed followingpacing in the ventricles. In some scenarios, the cardiac signal analyzedfor cardiac response determination may comprise the integral or thederivative of the sensed signal.

According to one morphology-based technique, the features of cardiacsignal sensed following pacing are extracted. The extracted features arecompared to template features characterizing a particular type ofcardiac pacing response through the use of feature correlationcoefficient analysis.

Some approaches for cardiac response determination are based oncancellation of depolarization wavefronts caused by paced or sensedcardiac events occurring in bilateral cardiac chambers, e.g., right andleft ventricles. In one exemplary situation, after sequentially pacingboth ventricles, the system senses for cardiac activity in thefirst-paced ventricle during a cross-chamber sensing window that followsthe pacing pulse delivered to the second-paced ventricle. If both pacingpulses captured their respective chambers, the depolarization wavefrontof the first-paced ventricle collides with a depolarization wavefront ofthe second-paced ventricle and cancels the cardiac activity in thefirst-paced ventricle during the cross chamber sensing window. If thefirst-paced ventricle was not captured, then no cancellation occurs, andcardiac activity responsive to the activation of the second pacedchamber is evident in the cross chamber sensing window.

In various other implementations, capture verification may be achievedby analysis of hemodynamic changes, analysis of impedance, analysis ofheart sounds and any other indicators of capture status.

In some embodiments, discrimination between capture, fusion, andnon-capture with or without intrinsic activity may be achieved. For eachof these response scenarios, the algorithm may implement a differentprocess for adjusting pacing parameters. For example, detection offusion is an indication that the pacing delay is slightly too long, andthe AVD_(L) may decreased 240 by an incremental amount to reduce thelikelihood of fusion for subsequent beats. Non-capture with or withoutintrinsic activation may indicate insufficient LV pacing energy. Ifnon-capture is detected, the algorithm implements 250 an increase in theLV pacing energy. If an intrinsic depolarization is detected along withthe non-capture determination, then the AVD_(L) may also be modified forthe next cycle.

If LV capture is detected, the pacing energy is sufficient to achievecapture and no adjustments are made 245 to the LV pacing energy. Thecurrent AVD_(L) is maintained for the next cardiac cycle. Optionally, asdescribed in more detail below, the AVD_(L) may be also adjusted tocompensate for changes in the cardiac rate.

The flow diagram of FIG. 2 illustrates adjustment of LV pacingparameters, although adjustment of the RV pacing delay and/or pacingenergy and/or adjustment of both the RV and LV pacing delays and/orpacing energies may be implemented in a same or similar manner. Table 1provides a summary of pacing delay and/or pacing energy adjustments thatmay be made according to one embodiment.

TABLE 1 Pacing response for current beat Basis for pacing parameteradjustments for next beat RV LV AVD_(R) AVD_(L) LV Pacing energy 1-1 C Sno change measured no change interval 1-2 C C no change no change nochange 1-3 C NC, no change no change increase by NC + I predeterminedamount; schedule LV automatic threshold test 1-4 C F no changeincremental no change 1-5 S S measured interval measured no changeinterval 1-6 S C measured interval no change no change 1-7 S NC measuredinterval no change increase by NC + I predetermined amount; schedule LVautomatic threshold test 1-8 S F measured interval incremental no change1-9 F S incremental measured no change interval  1-10 F C incremental nochange no change  1-11 F NC incremental no change increase by NC + Ipredetermined amount; schedule LV threshold test  1-12 F F incrementalincremental  1-13 NC X If RV loss of capture is detected, increase RVpacing energy by a predetermined amount and schedule RV automaticthreshold test

Table 1 illustrates 13 CRT pacing scenarios labeled 1-1 through 1-13along with the basis for modification of pacing parameters for the nextbeat. During any cardiac cycle, one or both ventricles may intrinsicallydepolarize prior to a scheduled pace; a sensed ventriculardepolarization is indicated by an S in Table 1. If the cardiac paceproduces a propagating wave of depolarization, the pace may producecapture (C) of the ventricle or a fusion beat (F). If the ventricle isnot captured by the pace, non-capture with or without intrinsicactivation is detected. These non-capture possibilities are denoted NC+Iand NC, respectively. In Table 1, an X denotes any possible pacingresponse, S, C, F, NC+I, and NC.

Consider, for example, scenario 1-1 listed in Table 1. In scenario 1-1,the RV pace of a cardiac cycle captures (C) the right ventricle. Anintrinsic LV depolarization (S) is sensed prior to delivery of the LVpace. On the next cycle, the AVD_(R) is maintained. The AVD_(L) isadjusted based on the measured interval between the atrial event and theintrinsic left ventricular depolarization, AVI_(L). In this example, thepacing energy of the RV pace and the LV pace remains unchanged becausethe RV pace produced capture, and because the LV intrinsicallydepolarized prior to delivery of an LV pace, providing no indicationthat the LV pacing energy is insufficient to produce capture.

Next, consider CRT pacing scenario 1-3 listed in Table 1. During acurrent cardiac cycle, the right ventricular pace produces capture (C)of the RV and the LV pace does not produce capture (NC) of the LV.Noncapture with intrinsic depolarization (NC+I) may be detected afterdelivery of the LV pace. On the next cardiac cycle, the RV pacinginterval, AVD_(R), is maintained. The LV pacing energy is increased by apredetermined amount. Optionally, the LV pacing interval, AVD_(L), isadjusted based on the measured AVI_(L), which is the interval measuredbetween the atrial event and the intrinsic depolarization of the LV. AnLV threshold test may be scheduled.

As a further example, consider CRT pacing scenario 1-4 listed inTable 1. During a current cardiac cycle, the RV pacing pulse producescapture (C) and a fusion beat (F) is detected following the LV pace.Thus, the LV pace appears to be of sufficient energy to produce capture,but the LV pace timing may be adjusted to decrease the likelihood offusion. In this scenario, the AVD_(R) remains unchanged and the AVD_(L)is decreased by an incremental amount to reduce the likelihood of fusionoccurring during the next cardiac cycle.

Table 1 illustrates other CRT pacing scenarios that may be interpretedin a similar manner to the examples provided above. In the exampleprovided by Table 1, if loss of capture is detected for the RV,regardless of the LV response, RV pacing energy is increased and an RVthreshold test is scheduled.

As previously discussed, CRT is delivered to improve a patient's cardiacpumping capability and is normally delivered in atrial tracking or AVsequential pacing modes. These pacing modes implement pacing delays suchas AVD_(R) and AVD_(L) to improve synchronization of ventricularcontractions. Optimally, the CRT pacing produces ventricularsynchronization during systole after optimal pre-load by the atrialcontractions. For optimal hemodynamics, it is desirable for the pacingdelays to vary with atrial rate in a manner similar to the way theintrinsic AV interval normally varies with atrial rate to produce morephysiologic pacing response. Variation in the pacing delays isespecially desirable during elevated atrial rates which may beexperienced more frequently by heart failure patients as the heart rateincreases to compensate for the loss of pumping ability.

Variations in the AVD_(R) and/or AVD_(L) may be implemented based on themeasured atrial rate which can be determined as the reciprocal of theinterval between atrial sensed or paced beats. In one exemplaryembodiment, rate-adjustments to the AVD_(R) and/or AVD_(L) are made forcardiac cycles that follow capture of the right and/or left ventricles,respectively and for cardiac cycles that follow non-capture of the rightand/or left ventricles. The pacing delays for cardiac cycles subsequentto a cycle in which some intrinsic activation occurs, i.e., sensedventricular depolarizations that inhibit ventricular pacing, fusionbeats, or non-captured beats with intrinsic activation, are not variedaccording to rate but are adjusted based on the measured AV intervals(AVI_(R) or AVI_(L)) of the previous cycle.

The flow diagram of FIG. 3A illustrates the concept of adjusting 305 thepacing delays AVD_(R) and/or AVD_(L) based on rate for cardiac cycles inwhich intrinsic ventricular depolarizations are absent and adjusting 310the CRT pacing delays AVD_(R) and/or AVD_(L) based on measured intrinsicintervals of the previous cycle for cardiac cycles in which intrinsicventricular depolarizations occur.

Whether one or more pacing delays AVD_(R) and/or AVD_(L) of a currentcardiac cycle are adjusted for rate or are set to be less than measuredintrinsic intervals AVI_(R) and/or AVI_(L) of the previous cardiac cycleis contingent on whether intrinsic depolarizations are sensed during thepacing delay(s) AVD_(R) and/or AVD_(L) during the previous cardiaccycle. If an intrinsic depolarization of a ventricle is sensed during acardiac cycle before delivery of the pacing pulse to a ventricle, forexample, then the associated intrinsic atrioventricular interval,AVI_(R) and/or AVI_(L), is measured 325 and the pacing delay(s), AVD_(R)and/or AVD_(L) used for the subsequent cardiac cycle are adjusted 310 tobe less than the measured interval AVI_(R) and/or AVI_(L).

After CRT pacing delays AVD_(R) and/or AVD_(L) for a cardiac cycle areset 305, 310, CRT pacing is scheduled 312. If no intrinsic right or leftventricular depolarizations are sensed 315 during the AVD_(R) and/orAVD_(L) intervals, respectively, then the right and left ventricularpacing is delivered as scheduled. The cardiac response to pacing isdetermined 330. If the CRT pacing results in capture of a ventricle, thepacing delay for that ventricle during the next cardiac cycle isadjusted 305 according to atrial rate. If the CRT pacing did not resultin capture for a ventricle, (i.e., non-capture or non-capture and anintrinsic beat, then the pacing energy for that ventricle is increased340 and the pacing cycle for the next cardiac cycle is adjusted 305according to atrial rate.

A fusion beat may occur following delivery of a pacing pulse. A fusionbeat results when the depolarization wavefront initiated by the pacecollides with an intrinsic depolarization wavefront very close to thepacing site. If the CRT pacing resulted in fusion of the right and/orleft ventricles, the AVD_(R) and/or AVD_(L) are decreased 345 by apredetermined amount for the next cardiac cycle. The AVD_(R) and/orAVD_(L) may also be adjusted 305 according to atrial rate.

The measured intrinsic AV intervals, AVI_(R) and/or AVI_(L), whichindicate AV conduction delays for right and left ventricles,respectively, may be used to update 313 a rate-indexed table of pacingdelays. Calculation of pacing delays AVD_(R) and/or AVD_(L) based onmeasured intrinsic AV intervals (AVI_(R) and/or AVI_(L)) and thedevelopment of a rate-indexed table of pacing delays based on measuredintrinsic AV intervals is described in more detail below.

The rate-indexed look-up table (or equations) for determining pacingdelays AVD_(R) and/or AVD_(L) may be initially determined and/orperiodically updated based on clinical hemodynamic testing wherein thepacing delays are optimized for cardiac function for at various atrialrates. For example, cardiac function may be measured in terms of dP/dt,arterial pulse pressure, or measurements of cardiac output.

Clinical hemodynamic testing to determine optimal pacing delays atvarious atrial rates can be time consuming and difficult to accomplish.As an alternative or as a supplement to such clinical hemodynamictesting to determine optimal pacing delays, determination of optimalrate-based pacing delays may be based on measured intrinsic intervalswhich are collected by the implanted device. As described in connectionwith FIG. 3A, adjustment of the pacing delay for a ventricle based onheart rate may occur if pacing of the ventricle is not inhibited and nointrinsic depolarization of the ventricle occurs during the cardiaccycle. The algorithms described herein allow the device to achieveconsistent capture of the RV and/or LV based on capture status duringCRT pacing, while also making adjustments to account for atrial rate.

In some embodiments, pacing delays such as the AVD_(R) and/or AVD_(L)are adjusted beat by beat based on measured atrial rate, measuredintrinsic intervals, and/or capture status of the previous beat. Thepacing scenarios illustrated in Table 2 are similar to those previouslydiscussed in connection with Table 1, except that the example of Table2, the pacing delay adjustment is based on atrial rate for cardiaccycles in which no intrinsic depolarization is sensed.

TABLE 2 Pacing response for Basis for pacing parameter current beatadjustments for next beat RV LV AVD_(R) AVD_(L) LV Pacing energy 2-1 C Srate measured no change interval 2-2 C C rate rate no change 2-3 C NC.rate rate increase; schedule NC + I LV threshold test 2-4 C F rateincremental no change 2-5 S S measured measured no change intervalinterval 2-6 S C measured rate no change interval 2-7 S NC, measuredrate increase; schedule NC + I interval LV threshold test 2-8 S Fmeasured incremental no change interval 2-9 F S incremental measured nochange interval  2-10 F C incremental rate no change  2-11 F NC,incremental rate increase; schedule NC + I LV threshold test  2-12 F Fincremental incremental no change  2-13 NC, X If RV loss of capture isdetected, increase RV NC + II pacing energy and perform RV automaticthreshold test

In pacing cycle scenario 2-1, for example, the RV pace captures theright ventricle and an intrinsic LV depolarization occurs prior todelivery of the LV pace. On the next cycle, the AVD_(R) is adjusted tocompensate for an increase or decrease in cardiac rate. The AVD_(L) isadjusted based on AVI_(L), which is the intrinsic AV interval measuredbetween the atrial event and the intrinsic LV depolarization of theprevious cardiac cycle. In this example, the pacing energy of the LVpace remains unchanged because there is no indication that the LV pacingenergy is insufficient to produce capture.

Next, consider CRT pacing scenario 2-3. During a cardiac cycle, theright ventricular pace produces capture of the RV and the LV pace doesnot produce capture of the LV, but an intrinsic LV depolarization isdetected after delivery of the LV pace. On the next cardiac cycle, theRV pacing interval, AVD_(R), is adjusted to compensate for any changesin rate. The LV pacing energy is increased by a predetermined amount andan LV capture threshold test may be scheduled. The LV pacing interval,AVD_(L), is adjusted based on the intrinsic interval AVI_(L).

Finally, consider CRT pacing scenario 2-4. During a cardiac cycle, theRV pacing pulse produces capture and a fusion beat is detected followingthe LV pace. Thus, the LV pace appears to be of sufficient energy toproduce capture, but the pacing timing may be adjusted to decrease thelikelihood of fusion. In this scenario, the RV pacing delay AVD_(R) maybe adjusted to compensate for changes in rate and the LV pacing delayAVD_(L) may be adjusted by an incremental decrease to reduce thelikelihood of fusion occurring during the next cardiac cycle.

After detection of an intrinsic depolarization, the pacing delay (AVD)for the next cardiac cycle is decreased to be less than the measuredintrinsic AVI of the previous cycle. In some embodiments, duringsubsequent cycles, the pacing delay is gradually increased until itmatches the pacing delay indicated by the rate-indexed look-up table.

Gradual increase in a pacing delay is illustrated by the flow diagram ofFIG. 3B. At the start of a pacing cycle 350, the device determines ifthe pacing delay AVD_(R) and/or AVD_(L) used for the immediatelyprevious cycle was less than 355 the rate-indexed look up table valuefor the previous cycle. If the pacing delay AVD_(R) and/or AVD_(L) wasnot less than 355 the rate-indexed value, then the pacing delay AVD_(R)and/or AVD_(L) for the current cycle is determined 305 (FIG. 3A) basedon atrial rate. If the pacing delay AVD_(R) and/or AVD_(L) for theimmediately previous cycle was less than 355 the rate-indexed value,then the pacing delay AVD_(R) and/or AVD_(L) has been shortened inresponse to an intrinsic depolarization that occurred during a priorcycle. The device determines 360 if the immediately previous cycleincluded an intrinsic depolarization (pace inhibited by a senseddepolarization, fusion or non-capture with intrinsic activation) byanalyzing the pacing delay AVD_(R) and/or AVD_(L). If the pacing delayAVD_(R) and/or AVD_(L) has been recently decreased, then the pacingdelay that was used for the immediately previous cycle is incrementallyincreased 365 and CRT pacing is scheduled 312 (FIG. 3A). If theimmediately previous cycle included 360 an intrinsic depolarization,then the pacing delay AVD_(R) and/or AVD_(L) for the next beat isdecreased 310 (FIG. 3A) to a value less than the measured intrinsicinterval AVI_(R) and/or AVI_(L). Incremental increases are made topacing delays AVD_(R) and/or AVD_(L) of subsequent cycles, so long as nointrinsic depolarizations occur, until the rate-indexed value isachieved.

The rate-based adjustments described herein may be made usingrate-indexed intrinsic interval data collected by the device over time.Appropriate adjustments to the pacing delays may be stored in a look-uptable indexed by rate and/or expressed as a function of rate orexpressed as a series of rate-indexed functions. One example of methodsand systems for implementation of rate-based adjustment of pacingintervals is described in commonly owned U.S. Pat. No. 7,123,960 whichis incorporated herein by reference.

CRT is used to control the conduction sequence of ventricularcontractions by applying ventricular paces to compensate for conductiondefects between and/or within the ventricles. For example, CRT isparticularly useful to treat left ventricular dysfunction which ariseswhen portions of the left ventricle contracts later than normal duringan intrinsic cardiac cycle. CRT pacing involving biventricular pacing orleft ventricle-only pacing compensates for the later than normalcontraction by pre-exciting the left ventricle with a first pacedelivered to the left ventricle followed by a right ventricular pace (orintrinsic depolarization).

The left ventricular pace excites the left ventricular free wall whilethe right ventricular pace excites the ventricular septum. The desiredsituation is simultaneous contraction of the left ventricular free walland septum (septum-free wall fusion). When clinical hemodynamic testingis performed on a population of subjects to determine the optimal valuesof the pacing delays, there is found to be a correlation between theoptimal delays for a particular subject and that subject's measuredright and left atrioventricular intervals, AVI_(R) and AVI_(L),respectively, during an intrinsic beat. As described more fully in U.S.Pat. No. 7,123,960, the optimum pacing delays for a particular patientmay be estimated from intrinsic conduction data in terms of specifiedcoefficients as:

AVD _(R) =k ₅ AVI _(R) +k ₆ AVI _(L) k ₇  [1]

and

AVD _(L) =k ₈ AVI _(R) +k ₉ AVI _(L) +k ₁₀  [2]

In order determine the specified coefficients, k₅ through k₁₀, clinicalpopulation data is obtained that relates particular values of themeasured intrinsic conduction parameters to an optimum value of thepre-excitation timing parameter as determined by concurrent measurementof another parameter reflective of cardiac function (e.g., maximum dP/dtor minimum atrial rate). A linear regression analysis is then performedto derive values of the specified coefficients used in the formula forsetting the pacing delays, the specified coefficients thus beingregression coefficients.

CRT pacing parameters that are adjusted for rate may be achieved bystoring a set of rate-indexed equations for AVD_(R) and/or AVD_(L), orby storing a look-up table of values which are calculated from theseequations or otherwise determined. These rate-based pacing delays may beused for pacing delay adjustment as described above for certain pacingcycles.

In an exemplary embodiment, the system computes the rate adjustedAVD_(R) and/or AVD_(L) intervals to be used for delivering CRT bycollecting intrinsic conduction data at different atrial rates. Theatrial rate may vary intrinsically or as the result of variations inpacing. The intervals AVI₂, and/or AVI_(L), are measured for variousrates and these intrinsic AVI_(R) and/or AVI_(L) intervals are used tocalculate, e.g., via the equations such as [1] and [2] above, pacingdelays which are stored in a rate-indexed look up table. For example,each measured AVI_(R) and/or AVI_(L) may be averaged or otherwisecombined with previously measured AVI_(R) and/or AVI_(L) intervals,respectively. The average or combination of these intrinsic intervalsare used to calculate or re-calculate rate-indexed pacing delays. Insome embodiments, the rate-indexed pacing delays AVD_(R) and/or AVD_(L)are stored as entries in a look up table. The rate-indexed look-up tableentries may be used to implement rate-based adjustment of CRT pacingdelays for subsequent cardiac cycles. The pacing delays used for CRTpacing may use the look up table entries and additional adjustments tothe look up table values may be made beat by beat based on whether anintrinsic depolarization occurred and/or on the capture status of aprevious cycle.

After development of a look up table based on measured intrinsicintervals for at least two atrial rates, the implantable device may varythe pacing delays as the atrial rate changes. One look up table entrymay correspond to a range of atrial rates. If there is no pacing delayvalue corresponding to a particular rate, the device may interpolatebetween pacing delay values for atrial rates above and below the presentrate to determine the rate adjusted pacing delay.

In some embodiments, rate-based pacing delays may be determined byanalyzing stored data related to the cardiac pacing response status(capture, non-capture, fusion, etc.) of previous cycles. From thisanalysis, pacing delays that produce superior capture performance foreach atrial rate can be stored for later use. According to thisapproach, the implantable cardiac device measures and stores in memorythe atrial rate, pacing delays, measured intrinsic intervals, and theresponse to pacing for a number of cardiac cycles. The storedinformation can be analyzed by the implantable device, apatient-external device, or by a human analyst to determine appropriaterate-based pacing delays that produce consistent capture during CRTpacing.

For example, if the stored data reveals that a particular pacing delayor pacing delay range used at a particular rate or rate range fails toproduce consistent CRT pacing, then the pacing delay for the rate orrate range may be decreased so that consistent biventricular or LVpacing is promoted. The analysis may be performed, for example, bycomparing, at each rate range of interest, the percentage or number ofpaced beats for each ventricular chamber to the percentage or number ofbeats in which intrinsic ventricular depolarizations inhibitedventricular pacing in the chamber. The analysis may also take intoaccount the percentage or number of paced beats that resulted incapture, non-capture, non-capture with intrinsic depolarization and/orfusion.

Processes for analyzing the stored data, computing pacing delays, and/orprogramming the implantable device with rate-indexed pacing delays maybe implemented by an external device, may be implemented by an implanteddevice, or both devices may be used to implement the procedure.Furthermore, these processes may be performed in fully automatic orsemi-automatic modes. For example, operating in an automatic mode, theimplantable device and the external device communicate via a telemetrylink. The external device receives from the implantable device data suchas electrogram signals, markers corresponding to sensed events, measuredintervals indexed by rate, cardiac pacing response information, and/orother data. The external device processes the information acquired fromthe implantable device to determine rate-indexed AVD_(R) and/or AVD_(L)pacing delays and programs the implantable device with a rate-indexedlook up table of pacing delays.

In another example of an automatic mode, the implantable device operatesindependently and automatically, analyzing electrogram data, measuredintervals, and pacing response status to determine the rate-indexedpacing delays and programs the rate-indexed table of pacing delays foruse in subsequent cycles.

Operating in a semi-automatic mode, the external device (e.g., externalprogrammer) or implantable device may provide for display of textualand/or graphical data and analyses, histograms, statistical analysis inan appropriate format for viewing by a clinical user. For example, theexternal device may analyze the measured intrinsic intervals, thecardiac pacing responses, and the cardiac rate data and present theanalysis to the user via a user interface of the external device. Theexternal device may present graphs indicating relationships betweenvarious cardiac pacing responses and cardiac rate, for example. Thisinformation can be presented via a display on the external device toassist the physician in selecting appropriate pacing delays that willachieve consistent CRT pacing. The user interface may be arranged toaccept inputs from the human analyst which cause the implantable deviceto be programmed with selected pacing delays. For example, in somesemi-automatic modes, the external device includes a user interfaceconfigured to generate a display of textual and/or graphical informationand to receive commands from a user, e.g., via a touch screen, keyboard,mouse, or other input device.

The external device and/or implantable device may determine recommendedpacing delays which are presented to the human analyst via the display.A user may accept pacing delay recommendations made by the device, ormay override these recommendations and select different pacing delayswhich are then programmed into the implantable device.

FIGS. 4A-C provide an illustrative example of a data analysis for LVbeats in 9 atrial rate ranges between and including the device's lowerrate limit (LRL) and the maximum tracking rate (MTR). FIGS. 4A-Cillustrate graphs that may be generated on a display for viewing by ahuman analyst to allow the analyst to review device performance or toselect rate-indexed pacing delays. Each of these graphs provides thepercentage of certain types of LV cycles for the 9 rate ranges. Similargraphs may be generated for RV cycles, however, for simplicity, only LVcycles are described in this example.

FIG. 4A provides the percentage of captured LV cycles for 9 rate ranges.FIG. 4B illustrates the number of LV cycles in which a sensed intrinsicLV depolarization inhibited the scheduled LV pace. FIG. 4C illustratesthe number of paced LV cycles that included a fusion beat or non-capturewith intrinsic activation. The number of LV cycles that resulted innon-capture without intrinsic activation may also be displayed, but thisgraph is not shown in this particular example. FIG. 5 illustrates analternate graph comprising a stacked bar graph that may be used todisplay multiple types of pacing cycles on the same set of axes.

The implantable device and/or the external device may take certainactions as a result of changes in the percentage of captured beatsachieved by the CRT pacing. For example, if the percentage of capturedbeats for the LV and/or RV in one or more rate ranges falls below aprogrammable threshold percentage, an alert may be generated and sent tothe clinician. Alternatively, the programmable threshold may beautomatically reprogrammed by the device with a notification of thechange sent to the clinician. The device may be configured to allow anylevel or frequency of notification and/or automaticity with regard toreprogramming device parameters as desired.

The device may analyze stored data and select pacing delays to achieveimproved device performance with the goal of achieving a higher numberof captured beats. A format for displaying recommended optimized pacingdelays which have been selected by the device is illustrated in FIG. 6,although alternate formats may be used. In FIG. 6, the recommendedoptimized AVD_(L) 605 is illustrated for each rate 610. As furtherillustrated in FIG. 6, the previous AVD_(L) 615 used for each rate andmeasured AVI_(L) 625 and measured AVI_(R) 630 for each rate may also bedisplayed to the user for comparison.

In some embodiments, the human analyst may accept or reject the pacingdelays recommended by the device for each rate and/or may substitutealternate pacing delays. For example, in some implementations, theanalyst may independently modify the recommended pacing delays for eachrate by operating scroll bars 620.

After the pacing delays for each rate have been selected, the device mayperform a simulation and display the results of the simulation to theuser. The simulation results may be displayed as bar graphs or stackedbar graphs similar to the graphs of FIGS. 5A and 5B, for example. Afterviewing the results of the simulation, if the user is satisfied with theselected pacing delays, the user may confirm the selections, causing thepacing delay selections to be uploaded to the implantable device.

A wide variety of cardiac devices may be configured to implementdetermination of pacing parameters in accordance with the presentinvention. A non-limiting, representative list of such devices includescardiac monitors, pacemakers, cardiovertors, defibrillators,resynchronizers, and other cardiac monitoring and therapy deliverydevices. These devices may be configured with a variety of electrodearrangements, including transvenous, endocardial, and epicardialelectrodes (i.e., intrathoracic electrodes), and/or subcutaneous,non-intrathoracic electrodes, including can, header, and indifferentelectrodes, and subcutaneous array or lead electrodes (i.e.,non-intrathoracic electrodes).

FIG. 7 illustrates a patient-implantable medical device (PIMD) that maybe used for CRT pacing in accordance with embodiments of the invention.In this example, the implantable device 700 includes an implantablepulse generator 705 electrically and physically coupled to anintracardiac lead system 710.

Portions of the intracardiac lead system 710 are inserted into thepatient's heart. The intracardiac lead system 710 includes electrodes751-758 configured to sense electrical cardiac activity of the heart anddeliver electrical stimulation to the heart. Additionally, the cardiacelectrodes 751-758 and/or other sensors may be used to sense thepatient's transthoracic impedance, and/or sense other physiologicalparameters, such as cardiac chamber pressure or temperature. Theelectrodes 751-758 shown in FIG. 7 illustrate one possible electrodearrangement. Many other electrode arrangements, including intracardiacand/or subcutaneous intrathoracic and non-intrathoracic electrodes, maybe used and are considered to fall within the scope of the invention.The lead system 710 may include wired and/or wirelessly coupledelectrodes and/or sensors. In wireless configurations, sensed signalsfrom these electrodes and/or sensors are wirelessly communicated to thePIMD and/or may be wirelessly coupled to a patient-external device.

Portions of the housing 701 of the pulse generator 705 may optionallyserve as one or multiple can or indifferent electrodes. The housing 701is illustrated as incorporating a header 789 that may be configured tofacilitate removable attachment between one or more leads and thehousing 701. The housing 701 of the PIMD may include one or more canelectrodes 782. The header 789 of the PIMD may include one or moreindifferent electrodes 781.

Communications circuitry is disposed within the housing 701 forfacilitating communication between the pulse generator 705 and apatient-external device, such as an external programmer or advancedpatient management (APM) system, for example. The communicationscircuitry may also facilitate unidirectional or bidirectionalcommunication with one or more implanted, external, cutaneous, orsubcutaneous physiologic or non-physiologic sensors, patient-inputdevices and/or information systems.

The pulse generator 705 may optionally incorporate sensors which areused to sense patient activity as well as various respiratory andcardiac related conditions. For example, sensors may be optionallyconfigured to sense respiration, snoring, activity level, chest wallmovements, rales, coughing, heart sounds, murmurs, and otherinformation. The patient activity information may be used in combinationwith rate information for optimal setting of device timings.

For example, the lead system 710 and pulse generator 705 of the CRM 700may operate to provide one or more transthoracic impedance sensors andcircuitry capable of acquiring the patient's respiratory waveform andderiving respiration-related information. The transthoracic impedancesensor may include, for example, one or more intracardiac electrodes751-758 positioned in one or more chambers of the heart. Theintracardiac electrodes 751-758 may be coupled to impedance drive/sensecircuitry positioned within the housing 701 of the pulse generator 705.Information from the transthoracic impedance sensor and/or an activitysensor may be used to adapt the rate of pacing to correspond to thepatient's activity and/or hemodynamic need.

The lead system 710 may include one or more cardiac pace/senseelectrodes 751-756 positioned in, on, or about one or more heartchambers for sensing electrical signals from the patient's heart and/ordelivering pacing pulses to the heart. The intracardiac sense/paceelectrodes 751-756, such as those illustrated in FIG. 7, may be used tosense and/or pace one or more chambers of the heart, including the leftventricle, the right ventricle, and/or the right atrium. In someembodiments, electrodes may be also provided for pacing the left atrium.The lead system 710 may include one or more defibrillation/cardioversionelectrodes 757, 758 for delivering defibrillation/cardioversion shocksto the heart.

In some embodiments, the pulse generator 705 includes circuitry fordetecting cardiac tachyarrhythmias and/or for controllinganti-tachyarrhythmia pacing, cardioversion and/or defibrillation therapyin the form of electrical stimulation pulses or shocks delivered to theheart through the electrodes of the lead system 710 and/or the housingelectrodes 781, 782.

In addition to controlling the therapy operations described above, thepulse generator 705 includes circuitry for implementing rate-indexedpacing delays for CRT pacing as described herein, including measuringcardiac rate, measuring intrinsic intervals, determining the response topacing, storing a look-up table with optimized pacing parameters and/orfor determining one or more pacing parameters, such as AVD_(L), AVD_(R)for CRT pacing.

In some embodiments, the pulse generator 705 may be configured totransfer sensed or derived information relevant to pacing parameterdetermination to a patient-external device. Following download of theimplantably sensed or derived information, the pacing parameterdetermination may be made automatically or semi-automatically by thepatient-external device with or without interaction with a humananalyst. Following determination of the pacing delays, the informationcan be uploaded to the pulse generator 705 and subsequently used tocontrol the timing of pacing pulses delivered to the heart in such a waythat promotes LV capture and improves cardiac function.

FIG. 8 is a block diagram of a cardiac therapy system that may beemployed to provide CRT pacing using pacing delays selected to promoteconsistent LV capture in accordance with embodiments of the invention.The various components of the system illustrated in FIG. 8 cooperate toperform algorithms that achieve pacing therapy operations as described,for example, by the flow diagrams of FIGS. 2, 3A, and 3B.

The cardiac system illustrated in FIG. 8 includes an external programmer890 and the pulse generator 700 having circuitry 800 enclosed within animplantable housing 701. The cardiac system also includes a lead systemdeploying various electrodes 751-758 which are electrically coupled tothe pulse generator circuitry 800. The pulse generator circuitry 800includes circuitry for receiving cardiac signals sensed via the cardiacelectrodes and delivering electrical stimulation energy to the heart inthe form of pacing pulses or defibrillation shocks. The circuitry 800 ofthe pulse generator 700 is encased and hermetically sealed in a housing701 suitable for implanting in a human body. Power to the pulsegenerator circuitry 800 is supplied by an electrochemical battery 880. Aconnector block (not shown) is attached to the housing 701 of the pulsegenerator 700 to allow for the physical and electrical attachment of thelead system conductors to the pulse generator 700.

The pulse generator circuitry 800 may comprise a programmablemicroprocessor-based system, including a control system 820 and a memory870. The memory 870 can be used to store parameters for various pacing,defibrillation, and sensing operations, along with other information forcontrolling therapy delivery. The memory 870 is capable of storing arate-indexed look up table that includes pacing delay values AVD_(L),AVD_(R). The memory may also store electrogram signal data, markerinformation, measured cardiac rates and intrinsic intervals, e.g.,AVI_(L), AVI_(R), and/or cardiac data. The stored data may be obtainedfrom long-term patient monitoring which may be used for determiningpatient condition trends and/or for other diagnostic purposes. Datastored in the memory 870 may be transmitted to a patient-external device890, such as a programmer unit or advanced pacing management server asneeded or desired.

The control system 820 and memory 870 may cooperate with othercomponents of the pulse generator circuitry 800 to implement sensing andtherapy operations of the cardiac system. The control system 820includes a cardiac response classification processor 825 that has thecapability to discriminate between various pacing responses, forexample, capture, fusion, non-capture, and non-capture with intrinsicactivation. The control system 820 also includes additional functionalcomponents, including a pacemaker control circuit 822 which includestiming circuitry for controlling CRT pacing using AVD_(L), and AVD_(R)pacing delays. The pulse generator circuitry 800 may also include anarrhythmia detector 821 and circuitry 850 for delivering defibrillationand/or cardioversion therapy to terminate detected tachyarrhythmias.

Telemetry circuitry 860 may be implemented to provide communicationsbetween the pulse generator circuitry 800 and the patient-externaldevice 890. In one embodiment, the telemetry circuitry 860 and theprogrammer unit 890 communicate using a wire loop antenna and a radiofrequency telemetric link to receive and transmit signals and databetween the external unit 890 and the telemetry circuitry 860. In thismanner, programming commands and other information may be transferredbetween the control system 820 and the external device 890.

The patient-external device 890 may be an external programmer oradvanced patient management (APM) system. The advanced patientmanagement system allows physicians or other personnel to remotely andautomatically monitor cardiac and/or other patient conditions. Via anAPM system, a physician may remotely alter therapy parameters, performdevice and/or patient diagnostic testing, and/or access informationstored in the implantable device. In one example, a cardiacpacemaker/defibrillator, or other device, may be equipped with varioustelecommunications and information technologies that enable real-timedata collection, diagnosis, and treatment of the patient via an APMsystem.

In the embodiment illustrated in FIG. 8, electrodes RA-tip 752, RA-ring751, RV-tip 753, RV-ring 756, RV-coil 758, SVC-coil 757, LV distalelectrode 755, LV proximal electrode 754, indifferent electrode 781, andcan electrode 782 are coupled through a switch matrix 810 to sensingcircuits 831-837.

A right atrial sensing circuit 831 serves to detect and amplifyelectrical signals from the right atrium of the heart. Bipolar sensingin the right atrium may be implemented, for example, by sensing voltagesdeveloped between the RA-tip 752 and the RA-ring 751. Unipolar sensingmay be implemented, for example, by sensing voltages developed betweenthe RA-tip 752 and the can electrode 782. Outputs from the right atrialsensing circuit 831 are coupled to the control system 820 where sensedatrial depolarization may be utilized to implement atrial trackingpacing modes, for example.

A right ventricular sensing circuit 832 serves to detect and amplifyelectrical signals from the right ventricle of the heart. The rightventricular sensing circuit 832 may include, for example, rightventricular rate channel sensing circuitry 833 and right ventricularshock channel sensing circuitry 834. Right ventricular cardiac signalssensed through use of the RV-tip 753 electrode are right ventricularnear-field signals, and are denoted rate channel signals. A bipolar RVsignal may be sensed as a voltage developed between the RV-tip 753 andthe RV-ring 756. Alternatively, bipolar sensing in the right ventriclemay be implemented using the RV-tip electrode 753 and the RV-coil 758.Unipolar sensing in the right ventricle may be implemented, for example,by sensing voltages developed between the RV-tip 753 and the canelectrode 782.

Right ventricular cardiac signals sensed through use of thedefibrillation electrodes are far-field signals and are denote shockchannel signals. More particularly, a right ventricular shock channelsignal may be detected as a voltage developed between the RV-coil 758and the SVC-coil 757. A right ventricular shock channel signal may alsobe detected as a voltage developed between the RV-coil 758 and the canelectrode 782. In another configuration the can electrode 782 and theSVC-coil electrode 757 may be electrically shorted and a RV shockchannel signal may be detected as the voltage developed between theRV-coil 758 and the can electrode 782/SVC-coil 757 combination.

Some embodiments may include circuitry and electrodes for sensing leftatrial signals. In these embodiments, electrodes are electricallycoupled to the left atrium and the pulse generator circuitry 800includes a left atrial sensing circuit which serves to detect andamplify electrical signals from the left atrium of the heart.

Optionally, an LV coil electrode (not shown) may be inserted into thepatient's cardiac vasculature, e.g., the coronary sinus, adjacent theleft heart. Signals detected using combinations of the LV electrodes,755, 754, LV coil electrode (not shown), and/or can electrode 782 may besensed and amplified by the left ventricular sensing circuitry 836.

Various combinations of the electrodes 771-758, 781 and 782 may beutilized in connection with pacing the heart. The pacemaker controlcircuit 822, in combination with pacing circuitry for the right atrium841, left ventricle 843, and right ventricle 844 generates pacing pulseswhich are delivered via electrode combinations selected from electrodes751-758, 781 and 782. The pacing electrode combinations may be used toeffect bipolar or unipolar pacing pulses to a heart chamber using one ofthe pacing vectors as described above.

The switching matrix 810 may be operated to couple selected combinationsof electrodes 751-758, 781 and 782 to the sensing circuits 831-835, thepacing and defibrillation circuits 841, 843, 844, 850 and/or an evokedresponse sensing circuit 837. The evoked response sensing circuit 837serves to sense and amplify signals developed using selectedcombinations of electrodes to discriminate between the various responsesto pacing in accordance with embodiments of the invention. The evokedresponse sensing circuit 837 is coupled to the cardiac responseclassification processor 825 which analyzes the output of the evokedresponse sensing circuit 837 to classify the cardiac pacing response.The cardiac signal sensed following delivery of a pacing pulse may beanalyzed to identify the response to pacing as left chamber captureonly, right chamber capture only, multi-chamber capture, fusion,non-capture, or non-capture with intrinsic activation, for example.

In some implementations, the pulse generator circuitry 800 may include asensor 861 that is used to sense the patient's activity or hemodynamicneed. In one implementation, the sensor may comprise, for example, anaccelerometer configured to sense patient activity. In anotherimplementation, the sensor 861 may comprise an impedance sensorconfigured to sense patient respiration. The output of the sensorindicates the patient's activity and/or hemodynamic requirements and maybe used to determine a sensor-indicated pacing rate. The pacing outputof the pulse generator 700 may be adapted based on the sensor-indicatedpacing rate signal to provide rate-adaptive pacing.

Various modifications and additions can be made to the preferredembodiments discussed hereinabove without departing from the scope ofthe present invention. Accordingly, the scope of the present inventionshould not be limited by the particular embodiments described above, butshould be defined only by the claims set forth below and equivalentsthereof.

What is claimed is:
 1. A method of operating a cardiac therapy system todeliver cardiac resynchronization therapy (CRT) pacing that includespacing at least a left ventricle, the method comprising: schedulingdelivery of the CRT pacing to one or both ventricles for a cardiaccycle; if an intrinsic depolarization of a ventricle is detected duringa pacing delay of the ventricle: inhibiting the scheduled CRT pacing tothe ventricle for the cardiac cycle; measuring an intrinsic interval ofthe ventricle for the cardiac cycle; decreasing a subsequent pacingdelay of the ventricle for a subsequent cardiac cycle to be less than orequal to the measured intrinsic interval; and determining if capture ofthe ventricle occurs for the subsequent cardiac cycle.
 2. The method ofclaim 1, wherein the pacing delay comprises one or more of a rightatrioventricular delay, a left atrioventricular delay, and aninterventricular delay.
 3. The method of claim 1, further comprisingincreasing the pacing delay of the ventricle by a predetermined amountduring one or more additional cardiac cycles following the subsequentcardiac cycle.
 4. The method of claim 1, wherein: scheduling the CRTpacing comprises scheduling the CRT pacing to both left and rightventricles; inhibiting the scheduled CRT pacing to the ventriclecomprises inhibiting the scheduled CRT pacing to one or both of the leftand right ventricles; measuring the intrinsic interval of the ventriclecomprises measuring intrinsic intervals of one or both of the left andright ventricles; and decreasing the subsequent pacing delay of theventricle comprises decreasing subsequent pacing delays of one or bothof the left and right ventricles.
 5. The method of claim 1, furthercomprising: if no intrinsic depolarization of the ventricle is detectedduring the pacing delay: delivering the CRT pacing to the ventricle asscheduled; determining a cardiac response to the pacing; and adjustingthe pacing delay of the ventricle for the subsequent cardiac cycle basedon the cardiac response to the delivered CRT pacing.
 6. The method ofclaim 5, wherein determining the cardiac pacing response comprisesdiscriminating between capture, fusion, and non-capture of theventricle.
 7. The method of claim 5, wherein adjusting the pacing delaybased on the cardiac pacing response comprises maintaining or increasingthe pacing delay if capture is determined as the pacing response.
 8. Themethod of claim 5, wherein adjusting the pacing delay based on thecardiac pacing response comprises incrementally decreasing the pacingdelay if fusion is determined as the pacing response.
 9. The method ofclaim 5, further comprising: measuring cardiac rate; and adjusting thepacing delay based on the measured cardiac rate.
 10. The method of claim9, wherein adjusting the pacing delay based on the cardiac pacingresponse and cardiac rate comprises adjusting the pacing delay based ona look-up table indexed by cardiac rate.
 11. The method of claim 9,further comprising adjusting one or more pacing energy parameters if thecardiac response is determined to be non-capture.
 12. A method ofsetting pacing delays for cardiac resynchronization therapy (CRT) pacingthat includes at least pacing the left ventricle, the method comprising:scheduling delivery of the CRT pacing for a cardiac cycle; measuringcardiac rate for the cardiac cycle; if an intrinsic depolarization of atleast one ventricle is detected during the pacing delay of the at leastone ventricle: inhibiting the scheduled CRT pacing to the ventricle; andmeasuring an intrinsic interval of the ventricle that is concluded bythe intrinsic ventricular depolarization; if no intrinsic depolarizationof the ventricle is detected during the pacing delay of the ventricle,determining a cardiac response to the CRT pacing, includingdiscriminating between capture, fusion, and non-capture of theventricle; storing information related to the measured cardiac rate, themeasured intrinsic interval, and the cardiac pacing response for aplurality of cardiac intervals; and presenting information to aclinician indicating relationships between the measured cardiac rate andthe cardiac pacing response for the plurality of cardiac intervals. 13.The method of claim 12, further comprising: analyzing the storedinformation to determine at least one recommended pacing delay based onone or more of the measured cardiac rate, the measured intrinsicinterval; and the cardiac pacing response for the plurality of cardiacintervals; and presenting the at least one recommended pacing delay tothe clinician via a user interface.
 14. The method of claim 13, furthercomprising analyzing the stored information to determine a look up tableof recommended pacing delays based on the measured cardiac rate, themeasured intrinsic interval; and the cardiac pacing response for theplurality of cardiac intervals.
 15. A cardiac therapy system capable ofdelivering cardiac resynchronization therapy (CRT) that includes pacingat least one ventricle, the system comprising: electrodes configured toelectrically couple to at least one of a right ventricle and a leftventricle; sensing circuitry configured to sense cardiac signals via theelectrodes, the cardiac signals including intrinsic depolarizationsignals; pacing circuitry configured to generate pacing pulsesdeliverable through the electrodes; cardiac response classificationcircuitry configured to determine cardiac responses to the pacingpulses; and pacing control circuitry configured to control the pacingcircuitry, the pacing control circuitry configured to schedule deliveryof CRT pacing to the at least one ventricle relative to a pacing delayfor the ventricle during a cardiac cycle to measure an intrinsicinterval of a ventricle that is concluded by an intrinsic ventriculardepolarization, to decrease a subsequent pacing delay for the ventricleof a number of subsequent pacing pulses to be less than or equal to themeasured intrinsic interval, and to confirm capture of at least onepacing pulse by the ventricle to determine an appropriate pacing delay.16. The cardiac therapy system of claim 15, wherein the pacing controlcircuitry is configured to further decrease the pacing delay foradditional cardiac cycles until the cardiac response classificationcircuitry determines that capture occurs.
 17. The cardiac therapy systemof claim 15, wherein the pacing control circuitry is further configuredto adjust a subsequent pacing delay of a subsequent cardiac cycle basedon the confirmed capture of the at least one pacing pulse by theventricle.
 18. The cardiac therapy system of claim 17, wherein thepacing control circuitry confirms the capture and adjusts the subsequentpacing delay on a beat to beat basis to maintain an appropriate pacingdelay.
 19. The cardiac therapy system of claim 15, wherein the pacingcontrol circuitry is further configured to deliver the CRT pacing if anintrinsic depolarization of the ventricle is not detected during thepacing delay of the cardiac cycle.
 20. The cardiac therapy system ofclaim 15, further comprising a sensor configured to generate an outputbased a patient's hemodynamic need, wherein the pacing control circuitryis further configured to adjust the pacing delay based on the sensoroutput.